System and method for preventing recurrence of atrial tachyarrhythmia

ABSTRACT

A system and method for providing pacing pulses after a cardioversion/defibrillation shock, where the pacing pulses have a pacing rate at an initial value. The pacing rate is decreased from the initial value until at least one intrinsic cardiac contraction is detected. In one embodiment, the pacing rate is decreased by a set amount after pacing a set number of cardiac cycles. Providing the set number of pacing pulses and decreasing the pacing rate by the set amount is then repeated until at least one intrinsic cardiac contraction is detected. An intrinsic cardiac rate is then determined from the at least one intrinsic cardiac contraction. The pacing rate is then increased and maintained to be above (i.e., greater than) the intrinsic cardiac rate.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a division of application Ser. No. 10/975,553, filedon Oct. 28, 2004, now U.S. Pat. No. 7,421,294, which is a division ofapplication Ser. No. 09/662,091, filed on Sep. 14, 2000, now U.S. Pat.No. 6,829,504, the specifications of which are incorporated herein byreference.

TECHNICAL FIELD

This invention relates generally to cardiac rhythm management systemsand particularly, but not by way of limitation, to a cardiac rhythmmanagement system and method for preventing recurrence of atrialtachyarrhythmias.

BACKGROUND

When functioning properly, the human heart maintains its own intrinsicrhythm, and is capable of pumping adequate blood throughout the body'scirculatory system. However, some people have irregular cardiac rhythms,referred to as cardiac arrhythmias. Such arrhythmias result indiminished blood circulation. One mode of treating cardiac arrhythmiasuses drug therapy. Drug therapy is not always effective for treatingarrhythmias of certain patients. For such patients, an alternative modeof treatment is needed. One such alternative mode of treatment includesthe use of a cardiac rhythm management system. Such systems are oftenimplanted in the patient and deliver therapy to the heart.

Cardiac rhythm management systems include, among other things,pacemakers, also referred to as pacers. Pacers deliver timed sequencesof low energy electrical stimuli, called pace pulses, to the heart, suchas via a transvenous lead wire or catheter (referred to as a “lead”)having one or more electrodes disposed in or about the heart. Heartcontractions are initiated in response to such pace pulses (this isreferred to as “capturing” the heart). By properly timing the deliveryof pace pulses, the heart can be induced to contract in proper rhythm,greatly improving its efficiency as a pump. Pacers are often used totreat patients with bradyarrhythmias, that is, hearts that beat tooslowly, or irregularly.

Cardiac rhythm management systems also include cardioverters ordefibrillators that are capable of delivering higher energy electricalstimuli to the heart. Defibrillators are often used to treat patientswith tachyarrhythmias, that is, hearts that beat too quickly. Suchtoo-fast heart rhythms also cause diminished blood circulation becausethe heart isn't allowed sufficient time to fill with blood beforecontracting to expel the blood. Such pumping by the heart isinefficient. A defibrillator is capable of delivering an high energyelectrical stimulus that is sometimes referred to as a defibrillationshock. The shock interrupts the tachyarrhythmia, allowing the heart toreestablish a normal rhythm for the efficient pumping of blood. Inaddition to pacers, cardiac rhythm management systems also include,among other things, pacer/defibrillators that combine the functions ofpacers and defibrillators, drug delivery devices, and any other systemsor devices for diagnosing or treating cardiac arrhythmias.

One problem faced by cardiac rhythm management systems is the propertreatment of atrial tachyarrhythmias, such as atrial fibrillation.Atrial fibrillation is a common cardiac arrhythmia which reduces thepumping efficiency of the heart, though not to as great a degree as inventricular fibrillation. However, this reduced pumping efficiencyrequires the ventricle to work harder, which is particularly undesirablein sick patients that cannot tolerate additional stresses. As a resultof atrial fibrillation, patients must typically limit their activity andexercise.

Although atrial fibrillation, by itself, is usually notlife-threatening, prolonged atrial fibrillation may be associated withstrokes, which are thought to be caused by blood clots forming in areasof stagnant blood flow. Treating such blood clots requires the use ofanticoagulants. Atrial fibrillation may also cause pain, dizziness, andother irritation to the patient. For this reason, atrial fibrillation istypically treated with a low energy defibrillation shock to enable theresumption of normal atrial heart rhythms.

An even more serious problem, however, is the risk that atrialfibrillation may induce irregular ventricular heart rhythms by processesthat are yet to be fully understood. Such induced ventriculararrhythmias compromise pumping efficiency even more drastically thanatrial arrhythmias and, in some instances, may be life-threatening.Moreover, treating atrial fibrillation by a defibrillation shock mayalso induce dangerous ventricular arrhythmias. For these and otherreasons, there is a need for safe and more effective atrial therapy thatprevents the occurrence of atrial tachyarrhythmias, such as atrialfibrillation, thereby avoiding inducing ventricular arrhythmia as theresult of the atrial tachyarrhythmia or its treatment.

SUMMARY

The present subject matter provides a system and method to address theaforementioned problems. In one embodiment, the present subject matterprovides a post-defibrillation shock therapy or post-cardioversiontherapy which may prevent or slow the recurrence of the arrhythmia whichnecessitated the shock. Pacing pulses are delivered at an elevated raterelative to normal intrinsic rates after delivering a defibrillation orcardioversion shock. The pacing pulses delivered at this rate initiateand control the contraction of the heart at a rate that is at or justabove the heart's own intrinsic rate. By controlling and initiating thecardiac contractions the likelihood of the arrhythmia which necessitatedthe shock returning is reduced.

In one embodiment, the present system provides forpost-defibrillation/cardioversion shock pacing pulses to be delivered tothe cardiac region having received the shock. The system begins bydelivering the pacing pulses at a predetermined time after thedefibrillation shock or cardioversion pulse has been delivered.Alternatively, pacing pulses of the present subject matter are deliveredafter treating the heart with antitachycardia pacing. The pacing pulsesare initially delivered at a pacing rate having an initial value. In oneembodiment, the initial value is set well above the intrinsic cardiacrate of the patient. This ensures that the pacing rate used by thesystem will control the rate and the refractory period of the heart. Inone embodiment, the pacing rate has an initial value set in the range of100 to 200 pacing pulses per minute.

The rate of the pacing pulses is decreased from the initial value downto a point where the intrinsic rate of the heart is detected. In oneembodiment, the decrease in the pacing rate occurs as a function ofdelivered pacing pulses. For example, the pacing rate is decreased by aset amount after a set number of cardiac cycles, where the set number ofcardiac cycles is a programmable number. In one embodiment, the setnumber of cardiac cycles paced and the decrease in the pacing rate bythe set amount is repeated until at least one intrinsic contraction isdetected.

As the pacing rate is being decreased, the system senses for theintrinsic cardiac contraction from the paced chamber. Once the intrinsiccontraction is sensed, an intrinsic cardiac rate is determined. In oneembodiment, the intrinsic cardiac rate is determined between the pacedevent and the intrinsic event. Alternatively, the intrinsic cardiac rateis determined between two consecutive intrinsic events (e.g., sensedcontractions). The pacing rate is then increased to be above theintrinsic rate, where the pacing rate is then maintained just above theintrinsic rate.

These and other features and advantages of the invention will becomeapparent from the following description of the preferred embodiments ofthe invention.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a flow chart illustrating one embodiment of the presentsubject matter.

FIG. 2 is a flow chart illustrating one embodiment of the presentsubject matter;

FIG. 3 is a graph of illustrating one embodiment of the present subjectmatter;

FIG. 4 is a schematic view of one embodiment of an implantable medicaldevice according to one embodiment of the present subject matter;

FIG. 5 is a schematic view of one embodiment of an implantable medicaldevice according to one embodiment of the present subject matter; and

FIG. 6 is a block diagram of one embodiment of an implantable medicaldevice according to the present subject matter.

DETAILED DESCRIPTION

In the following detailed description, references are made to theaccompanying drawings that illustrate specific embodiments in which theinvention may be practiced. Electrical, mechanical, programmatic andstructural changes may be made to the embodiments without departing fromthe spirit and scope of the present invention. The following detaileddescription is, therefore, not to be taken in a limiting sense and thescope of the present invention is defined by the appended claims andtheir equivalents.

Providing pacing pulses to a cardiac chamber soon after a defibrillationshock or a cardioversion pulse is delivered may prevent or slow therecurrence of the arrhythmia which necessitated the shock. It has beenfound that delivering pacing pulses at an elevated rate relative tonormal intrinsic rates allows for the rhythm of the heart to be bettercontrolled and the likelihood that an arrhythmia will reoccur lessened.For example, after delivering a defibrillation shock a cardiac chamberis paced at an elevated rate for a period of time, after which thepacing rate is gradually reduced (smoothing the pacing rate) down to thepoint where the pacing is stopped and the heart's intrinsic rhythm isallowed to resume control. By providing pacing pulses to the cardiacchamber, not only can the contraction rate of the heart be controlled,but the refractory periods of the chamber can be regularized.Regularizing the refractory periods of the cardiac chamber is importantin maintaining sinus rhythm (i.e., normal rhythm) of the heart. Once thepacing is stopped, and the heart's own intrinsic rhythm takes over,there is an increased opportunity for irregular refractory periods tooccur. Irregular refractory periods increase the chances that thearrhythmia, (e.g., fibrillation or tachycardia) will return. Thus,maintaining pacing control over the heart after a defibrillation shockor cardioversion pulse is important in ensuring that the heart maintainssinus rhythm.

One difficulty with maintaining pacing control over the cardiac chamberis balancing the heart's own intrinsic rate with what elevated pacingrate to use in maintaining control. Provide a pacing rate that is toomuch above the intrinsic rate may not be desirable for both the patientand for the longevity of the implantable device. Therefore, a systemwhich would allow for elevated pacing, post-defibrillation shock orcardioversion pulse, which would smooth to a pacing rate at or justabove the heart's own intrinsic rate is needed.

The present subject matter offers such a system. In one embodiment, thepresent system provides for post-defibrillation/cardioversion shockpacing pulses to be delivered to the cardiac region having received theshock. The pacing pulses are initially delivered at a pacing rate havingan initial value. In one embodiment, the initial value is set well abovethe intrinsic cardiac rate of the patient. This ensures that the pacingrate used by the system will control the rate and the refractory periodof the heart.

In one embodiment, the system begins by delivering the pacing pulses ata predetermined time after a defibrillation shock or cardioversion pulsehas been delivered. Alternatively, pacing pulses of the present subjectmatter are delivered after treating the heart with antitachycardiapacing. The rate of the pacing pulses is then decreased from the initialvalue down to a point where the intrinsic rate of the heart is detected.In one embodiment, the decrease in the pacing rate occurs as a functionof delivered pacing pulses, where the pacing rate is decreased by a setamount after a set number of cardiac cycles, where the set number ofcardiac cycles is a programmable number.

As the pacing rate is being decreased, the system senses for anintrinsic cardiac contraction from the paced chamber. Once the intrinsiccontraction is sensed, an intrinsic cardiac rate is determined. In oneembodiment, the intrinsic cardiac rate is determined between the pacedevent and the intrinsic event. Alternatively, the intrinsic cardiac rateis determined between two consecutive intrinsic events (e.g., at leasttwo sensed intrinsic contractions, such as intrinsic atrial contractionsor intrinsic ventricular contractions). The pacing rate is thenincreased to be above the intrinsic rate, where the pacing rate is thenmaintained just above the intrinsic rate, as will be more fullydescribed below.

Referring now to FIG. 1, there is shown one embodiment of a methodaccording to the present subject matter. At 100, an cardiac signal issensed from one or more cardiac chambers of the heart. In oneembodiment, the cardiac signal is either a unipolar signal or a bipolarsignal sensed with one or more electrodes implanted within the heart. At110, the cardiac signal is analyzed to detect an arrhythmia, such as afibrillation or a tachycardia episode. If an arrhythmia is not detected,the method continues to sense and analyze the cardiac signal. If,however, an arrhythmia is detected, one or more defibrillation shocks,or cardioversion pulses, are used to capture and convert the heart 120.Alternatively, under the appropriate circumstances, antitachycardiapacing is delivered to convert the arrhythmia (e.g., ventriculartachycardia) by stimulating the heart with a rapid series of electricalpulses.

Once captured and converted, pacing pulses having a pacing rate at aninitial value are provided to the heart at 130. In one embodiment, thefirst pacing pulse of the pacing pulses is provided at a delay after thedefibrillation or cardioversion shock. In one embodiment, the delay isprogrammable in the range of 0 milliseconds to 1000 milliseconds. In anadditional embodiment, the delay is programmable in the range of 0milliseconds to 500 milliseconds. These given time ranges for delay,however, are exemplary and other time ranges which exceed 1000milliseconds are considered within the scope of the present subjectmatter.

In an additional embodiment, the initial value of the pacing rate is set(programmed) at a value equal to or less than the maximum programmablepacing rate value of the implantable pacemaker in which the presentsubject matter is implemented. For example, the initial value of thepacing rate is set in the range of 100 to 200 pacing pulses per minute(interval durations of 600 to 300 milliseconds). In one embodiment,setting the initial value of the pacing rate includes either fixing thevalue of the pacing rate or allowing the pacing rate to be aprogrammable value. In one embodiment, the initial value of the pacingrate is a programmable value that is set above the intrinsic cardiacrate of the patient, where the intrinsic cardiac rate of the patient isdetermined by the patient's physician. Alternatively, the initial valueof the pacing rate is preset and is not adjustable.

The initial value of the pacing rate is used in pacing the heart for aset number of cardiac cycles. In one embodiment, the set number ofcardiac cycles is a programmable value in the range of two (2) toone-hundred twenty eight (128) cardiac cycles. Once the heart has beenpaced at the pacing rate initial value for the set number of cardiaccycles, the pacing rate is then decreased at 140. In one embodiment, thepacing rate is decreased by a set amount for every subsequent set of thenumber of cardiac cycles until an intrinsic cardiac contraction isdetected. Thus, providing the set number of pacing pulses and thendecreasing the pacing rate by the set amount is repeated until anintrinsic cardiac contraction is detected. In other words, the pacingrate for each of the set number of cardiac cycles becomes slower andslower, until an intrinsic cardiac contraction is detected.

The pacing rate is then decreased by adding a set value to the intervalduration between the pacing pulses. In one embodiment, the set value isin the range of seven and one-half (7.5) milliseconds to ten (10)milliseconds. Thus, for an initial pacing rate of 200 pacing pulses perminute and a set value of 10 milliseconds, after the first decrease thepacing rate would be approximately 193.5 pacing pulses per minute, afterthe second decrease the pacing rate would be approximately 187.5 pacingpulses per minute, and so forth until an intrinsic cardiac contractionis detected. In an alternative embodiment, the set value includesadditional values which allow for changes to the pacing rate accordingto the present subject matter (e.g., set values less than 7.5milliseconds and set values greater than 10 milliseconds).

At 150, once the intrinsic contraction is detected, an intrinsic cardiacrate is determined. In one embodiment, the intrinsic cardiac rate is therate determined from the time interval between the paced cardiac eventand the subsequent intrinsic cardiac event. In an alternativeembodiment, the intrinsic rate is determined from two consecutive sensedintrinsic cardiac contractions. Once the intrinsic cardiac rate isdetermined at 150, the pacing rate is increased at 160 to be greaterthan the intrinsic cardiac rate. In one embodiment, the pacing rate isincreased by subtracting the value to the interval duration between thepacing pulses. Thus, once the intrinsic rate is determined the cardiacpacing rate is increased by the margin of the value so the pacing pulsescontrol the contraction of the heart, and not the intrinsic mechanismsof the heart (i.e., the SA-node). The increased pacing rate is then usedin delivering the pacing pulse after the intrinsic pulse is detected.

The system then returns to 140, where the pacing rate is alloweddecrease as previously described until the next intrinsic contraction isdetected. The system then proceeds to 150, where the intrinsic rate isdetermined as previously described. The system then proceed through 160and back to 140. This allows the heart to be paced at, or nearly at, theintrinsic rate, while still being under the control of a pulsegenerator. Thus, the pacing rate is maintained at or above the intrinsiccardiac rate. As previously discussed, this allows the refractory periodof the cardiac chamber to be controlled so as to reduce the likelihoodof recurrence of the arrhythmia or tachyarrhythmia.

The post-shock therapy of the present subject matter is thendiscontinued after a predetermined time interval. In one embodiment, thepredetermined time interval is a programmable or a set value of up to 15minutes. After the predetermined time interval expires, the systemresumes any previously suspended pacing protocols and returns to sensethe cardiac signal from one or more cardiac chambers of the heart at100. Alternatively, the post-shock therapy according to the presentsubject matter is discontinued and the system returns to 100 after apredetermined number of intrinsic pulses are detected. In oneembodiment, the predetermined number of intrinsic pulses is programmedor set in the range of 0 to 15 sensed intrinsic pulses.

Referring now to FIG. 2, there is shown an additional embodiment of amethod according to the present subject matter. The embodiment of FIG. 2is specific to atrial arrhythmias and where pacing pulses are deliveredto the atrium. It will be appreciated that the present subject mattercan be applied to other cardiac regions, including, but not limited to,ventricular chambers of the heart (e.g., right and/or left ventricles)and/or atrial chambers of the heart (e.g., right and/or left atria).

At 200, an atrial signal is sensed from the atrium. In one embodiment,the atrial signal is either a unipolar signal or a bipolar signal sensedwith one or more electrodes implanted within the heart. At 210, theatrial signal is analyzed to detect an atrial fibrillation or atrialtachycardia. In one embodiment, the atrial rate is used as a criteriafor determining the presence of an atrial fibrillation and/or atrialtachycardia. Other techniques of determining the occurrence of atrialfibrillation and/or atrial tachycardia are possible. If an atrialfibrillation or tachycardia are not detected, the method continues tosense and analyze the atrial signal. If an atrial fibrillation ortachycardia is detected, one or more atrial defibrillation shocks, oratrial cardioversion pulses, are used to capture and convert the atrialchambers at 220.

Once captured and converted, pacing pulses having a pacing rate at aninitial value are provided to the atrium at 230. In one embodiment, afirst pacing pulse of the pacing pulses is provided at a delay after thedefibrillation or cardioversion shock. In one embodiment, the delay isprogrammable in the range of 0 milliseconds to 1000 milliseconds. In anadditional embodiment, the delay is programmable in the range of 0milliseconds to 500 milliseconds. These given time ranges for delay,however, are exemplary and other time ranges which exceed 1000milliseconds are considered within the scope of the present subjectmatter.

In an additional embodiment, the initial value of the pacing rate is set(programmed) at a value equal to or less than the maximum programmablepacing rate value of the implantable pacemaker in which the presentsubject matter is implemented. For example, the initial value of thepacing rate is set in the range of 100 to 200 pacing pulses per minute(interval durations of 600 to 300 milliseconds). In one embodiment,setting the initial value of the pacing rate includes either fixing thevalue of the pacing rate or allowing the pacing rate to be aprogrammable value. In one embodiment, the initial value of the pacingrate is a programmable value that is set above the intrinsic cardiacrate of the patient, where the intrinsic cardiac rate of the patient isdetermined by the patient's physician. Alternatively, the initial valueof the pacing rate is preset and is not adjustable.

The initial value of the pacing rate is used in pacing the atrium for aset number of cardiac cycles. In one embodiment, the number of cardiaccycles is a programmable value in the range of two (2) to one-hundredtwenty eight (128) cardiac cycles. Once the atrium has been paced at thepacing rate initial value for the set number of cardiac cycles, thepacing rate is then decreased at 240. In one embodiment, the pacing rateis decreased by a set amount for every subsequent set of the set numberof cardiac cycles until an intrinsic atrial contraction is detected.Thus, providing the set number of pacing pulses and then decreasing thepacing rate by the set amount is repeated until an intrinsic atrialcontraction is detected. In other words, the pacing rate for each groupof the set number of cardiac cycles becomes slower and slower, until anintrinsic atrial contraction is detected. In one embodiment, the pacingrate is decreased by adding the value to the interval duration betweenthe pacing pulses, where the value is in the range of seven and one-half(7.5) milliseconds to ten (10) milliseconds. Thus, for an initial pacingrate of 200 pacing pulses per minute and a set value of 10 milliseconds,after the first decrease the pacing rate would be approximately 193.5pacing pulses per minute, after the second decrease the pacing ratewould be approximately 187.5 pacing pulses per minute, and so forthuntil an intrinsic cardiac contraction is detected. In an alternativeembodiment, the set value includes additional values which allow forchanges to the pacing rate according to the present subject matter(e.g., set values less than 7.5 milliseconds and set values greater than10 milliseconds).

At 250, once the intrinsic contraction is detected, an intrinsic atrialrate is determined. In one embodiment, the intrinsic atrial rate is therate determined from the time interval between paced atrial event andthe subsequent intrinsic atrial event. In an alternative embodiment, theintrinsic rate is determined from two consecutive sensed intrinsicatrial contractions. Once the intrinsic atrial rate is determined at250, the pacing rate is increased at 260 to be greater than theintrinsic atrial rate. In one embodiment, the pacing rate is increasedby subtracting the value to the interval duration between the pacingpulses. Thus, once the intrinsic rate is determined the atrial pacingrate is increased by the margin of the value so the pacing pulsescontrol the contraction of the atrium, and not the intrinsic mechanismsof the heart (i.e., the SA-node). The increased pacing rate is then usedin delivering the pacing pulse after the intrinsic pulse is detected.

The system then returns to 240, where the pacing rate is alloweddecrease as previously described until the next intrinsic contraction isdetected. The system then proceeds to 250, where the intrinsic rate isdetermined as previously described. The system then proceed through 260and back to 240. This allows the atrium to be paced at, or nearly at,the intrinsic rate of the atrium, while still being under the control ofthe pulse generator. Thus, the pacing rate of the atrium is maintainedat or above the intrinsic rate of the atrium. As previously discussed,this allows the refractory period of the cardiac chamber to becontrolled so as to reduce the likelihood of recurrence of thearrhythmia or tachyarrhythmia.

The post-shock therapy of the present subject matter is thendiscontinued after a predetermined time interval. In one embodiment, thepredetermined time interval is a programmable or a set value of up to 15minutes. After the predetermined time interval expires, the systemresumes any previously suspended pacing protocols and returns to sensethe cardiac signal from one or more cardiac chambers of the heart at200. Alternatively, the post-shock therapy according to the presentsubject matter is discontinued and the system returns to 200 after apredetermined number of intrinsic pulses are detected. In oneembodiment, the predetermined number of intrinsic pulses is programmedor set in the range of 0 to 15 sensed intrinsic pulses.

Referring now to FIG. 3, there is shown an example of a post-therapypacing response according to the present subject matter. FIG. 3 shows aplot of an intrinsic cardiac rate 300 and a pacing rate 310 which areplotted on a rate (beats/time) versus time plot. At 320 a defibrillationor cardioversion shock has been delivered to the heart. No intrinsiccardiac rate is present at this time as the heart is in its refractoryperiod following the shock. Pacing pulses are delivered to the heartafter the delay 330, where the pacing pulses are delivered at theinitial value 340.

After the set number of paced cardiac cycles 350, the pacing rate isdecreased along 360, as previously described. The pacing rate isdecreased along 360 as previously described until an intrinsic atrialcontraction is detected at 370. Once the intrinsic atrial rate isdetermined, the pacing rate is then increased at 380 and the pacing rateis maintained at or above the intrinsic rate at 390, as previouslydescribed.

In one embodiment, the system of the present subject matter can have aprogrammable time interval over which the system will operate before theheart is allowed to revert to an intrinsic cardiac rhythm. In oneembodiment, the programmable time interval is set in the range of 15seconds to 1 hour. After this interval, the system would then revertback to any original settings for atrial pacing that might have beenprogrammed into the device.

Referring now to FIG. 4, there is shown one embodiment of a cardiacrhythm management system 400 according to the present subject matter. Inthe present embodiment, the cardiac rhythm management system 400includes a first cardiac lead 410 having a first electrode 414 and asecond electrode 416. In one embodiment, the first electrode 414 is apace/sense electrode located at or near a distal end 420 of the firstcardiac lead 410. The second electrode 416 is also a pace/senseelectrode located proximal the first electrode 414. In one embodiment,the second electrode 416 is a ring electrode which partially orcompletely encircles the first cardiac lead 410.

In one embodiment, the first electrode 414 is used to sense either aunipolar cardiac signal between the first electrode 414 and the housing428 of the cardiac rhythm management system 400. Alternatively, thefirst electrode 414 and the second electrode 416 are used to sense abipolar cardiac signal. In the present embodiment, the first cardiaclead 410 is a J-tip lead, where the first electrode 414 is located atthe distal tip of the lead 410.

The cardiac rhythm management system 400 further includes a secondcardiac lead 430. In one embodiment, the second cardiac lead 430includes a first pace/sense electrode 432, a first defibrillationelectrode 434 and a second defibrillation electrode 436. The secondcardiac lead 430 is implanted with the distal end of the lead implantedin the right ventricle of the heart, with the first defibrillationelectrode 434 located in the right ventricular chamber and the seconddefibrillation electrode 436 located in the right atrium and/or majorvein leading to the right atrium (e.g., superior vena cava). With thesecond lead 430, ventricular cardiac signals can be sensed between theelectrodes. For example, a rate signal (near field signal) is sensedbetween either the first pace/sense electrode 432 and the firstdefibrillation electrode 434, or between the first pace/sense electrode432 and the housing 428. A far field signal can also be sensed betweenthe first and second defibrillation electrodes 434 and 436. In oneembodiment, defibrillation and cardioversion pulses are deliveredbetween the first defibrillation electrode 434, and the seconddefibrillation electrode 436 and the housing 428, as shown by arrows440. The defibrillation and cardioversion pulses are delivered, in thepresent example, in response to an atrial arrhythmia as previouslydescribed. Alternatively, the defibrillation and/or cardioversion pulsescould be delivered in response to a ventricular arrhythmia.

The cardiac rhythm management system 400 includes control circuitrycoupled to the first electrode 414 and the second electrode 416 fromwhich a cardiac signal is sensed. The first electrode 414 and the secondelectrode 416 are shown implanted in a supraventricular region (i.e.,atrial region) of the heart, from which an atrial cardiac signal can besensed and to which pacing pulses can be delivered according the presentsubject matter. In one embodiment, pacing pulses can be deliveredbetween either the first electrode 414 and the housing 428 or the firstelectrode 414 and the second electrode 416. In addition, atrialdefibrillation shocks and/or cardioversion pulses can be delivered bythe control circuitry between the first defibrillation electrode 434,and the second defibrillation electrode 436 and the housing 428, asshown by arrows 440.

FIG. 4 also shows a medical device programmer 444. The medical deviceprogrammer 444 and the cardiac rhythm management system 400 includecommunication circuitry which allows for cardiac data to be to and fromthe cardiac rhythm management system 400. In addition, command signalsfor controlling the operation of the cardiac rhythm management system400 can also be sent between the medical device programmer 444 and thecardiac rhythm management system 400. In one embodiment, communicationbetween the medical device programmer 444 and the cardiac rhythmmanagement system 400 is established over a radio frequency telemetrychannel.

Referring to FIG. 5, there is shown an additional embodiment of thesystem shown in FIG. 4, where in addition to a first and second cardiaclead 410 and 430, there is shown a third cardiac lead 500 having atleast one defibrillation electrode 510. In one embodiment, the thirdcardiac lead 500 is positioned in a supraventricular location with atleast one defibrillation electrode 510 positioned within the coronarysinus and/or great cardiac vein. With the addition of the third cardiaclead 500, cardioversion and/or defibrillation pulses can be deliveredbetween any number of the defibrillation electrodes. For example,cardioversion/defibrillation pulses can be delivered betweendefibrillation electrode 510 and the second defibrillation electrode 436and the housing 428. Other shocking patterns are also possible andconsidered within the scope of the present subject matter.

Referring now to FIG. 6, there is shown one embodiment of a cardiacrhythm management system according to the present subject matter. Thesystem includes an implantable cardiac rhythm management device 600, afirst cardiac lead 602 and a second cardiac lead 604 (not to scale). Inthe embodiment shown in FIG. 6, the first cardiac lead 602 is shown witha first electrode 606 and a second electrode 607, and the second cardiaclead 604 is shown with a first electrode 608, a first defibrillationelectrode 610 and a second defibrillation electrode 612. In oneembodiment, the first electrode 606 and the second electrode 607 arepace/sense electrodes, where the first electrode 606 is a porous tipelectrode positioned at a distal end 614 of the first cardiac lead 602and the second electrode 607 is a ring electrode either partially orcompletely encircling the first cardiac lead 602 and is positionedproximal to the first electrode 606. The first electrode 608 is also apace/sense electrode positioned at the distal end 616 of the secondcardiac lead 604.

In one embodiment, the first electrode 606 and the second electrode 607of the first cardiac lead 602 are implanted within the supraventricularregion of the heart as previously described. The second cardiac lead 604is implanted within the heart, where the distal end of the lead 604 isimplanted at the apex of the right ventricle to allow the firstelectrode 608 and the first defibrillation electrode 610 to be withinthe right ventricular chamber of the heart and the second defibrillationelectrode 612 in the supraventricular region of the heart. In oneembodiment, the first electrode 608 and the first defibrillationelectrode 610 are used to detect a near field signal (a rate signal) andthe first defibrillation electrode 610 and the second defibrillationelectrode 612 are used to detect a far field signal (a morphologysignal) from the heart.

The electrodes are connected to electronic circuitry within theimplantable cardiac rhythm management device 600 through lead conductorshoused and electrically insulated within the body of the first andsecond cardiac leads 602 and 604. The lead conductors are coupled tolead connectors on the cardiac leads, which allow for the electrodespositioned on the leads to be coupled to the electronic circuitrythrough input terminals 620, 622, 624, 626 and 628. In one embodiment,the first and second cardiac leads 602 and 604 have elongated bodiesmade of one or more materials suitable for implantation in a human body,where such materials are known. Additionally, the electrodes areconstructed of electrically conductive materials, such as platinum,platinum-iridium alloys, or other alloys as are known. The leadconductors are also constructed of electrically conductive materialssuch as MP35N, an alloy of nickel, chromium, cobalt, and molybdenum.

The implantable cardiac rhythm management device 600 includes controlcircuitry 630, where the control circuitry 630 is coupled to theelectrodes 606, 607, 608, 610 and 612, from which at least a firstcardiac signal is sensed, electrical energy pulses are generated underpredetermined conditions, and providing electrical energy to electrodespositioned on the leads under the predetermined conditions. In oneembodiment, the control circuitry 630 is a programmablemicroprocessor-based system, with a microprocessor 632 and a memorycircuit 634, which contains parameters for various pacing and sensingmodes and stores data indicative of cardiac signals received by thecontrol circuitry 630. The control circuitry 630 is shown having variousmodules, which are implemented either in hardware or as one or moresequences of steps carried out on the microprocessor or othermicrocontroller. It is understood that the various modules of controlcircuitry 630 need not be separately embodied, but may be combined orotherwise implemented differently, such as in software/firmware.

The control circuitry 630 includes a pacing pulse generator 640, a pulserate controller 644, and an intrinsic rate detector 650 which arecoupled through bus 654. In one embodiment, the pacing pulse generator640 produces pacing pulses to be delivered through at least the firstelectrode, where the pacing pulse generator 640 is controlled by thepulse rate controller 644 to generate pacing pulses at the pacing rate,as previously described.

The implantable cardiac rhythm management device 600 further includes afirst sensor 656 coupled to input terminals 626 and 628 to allow for abipolar cardiac signal to be sensed through the first and secondelectrodes 606 and 607. Alternatively, a unipolar cardiac signal couldbe sensed between the first electrode 606 and the housing 658 of theimplantable cardiac rhythm management device 600. In addition to thefirst sensor 656, the implantable cardiac rhythm management device 600further includes a second sensor 660 and a third sensor 664. In oneembodiment, first and second defibrillation electrodes 610 and 612 arecoupled to second sensor 660 to allow for a bipolar morphology signal tobe sensed between the electrodes. In addition, first electrode 608 andfirst defibrillation electrode 610 are coupled to the third sensor 664to allow for a bipolar rate signal to be sensed between the electrodes.The pacing pulse generator 640 is coupled to at least the firstelectrode 606 and produces electrical pulses to be delivered to thefirst electrode 606, as previously described. Power to the implantablecardiac rhythm management device 600 is supplied by an electrochemicalbattery 668 that is housed within the device 600.

The output of each of the sensors 656, 660 and 664 is received by anarrhythmia detector 670. In one embodiment, the arrhythmia detector 670analyzes the sensed cardiac signals for the occurrence of sensed cardiaccontractions and the presence of arrhythmias. In one embodiment, thearrhythmia detector 670 analyze the cardiac signal being detected fromthe atrial region for the occurrence of an atrial arrhythmia. When anatrial arrhythmia is detected, one or more pulses of cardioversionand/or defibrillation energy are generated by thecardioversion/defibrillation pulse generator 672. The energy can then bedelivered to the atrial region through combinations of the firstdefibrillation electrode 610, second defibrillation electrode 612 andhousing 658 to convert the atrial arrhythmia, as previously described.Alternatively, the pacing pulse generator 640 generates antitachycardiapacing for delivery to the atria to convert the atrial arrhythmia, aspreviously described.

Once the atrial arrhythmia is converted, the pulse rate controller 644controls the pacing pulse generator 640 to generate pacing pulses at apacing rate having the initial value, as previously described. In oneembodiment, the pulse rate controller 644 controls the pacing pulsegenerator 640 to provide the first pacing pulse of the pacing pulses atthe delay after the electrical pulse, as previously described. The pulserate controller, through the pacing pulse generator 640, provides pacingpulses to generate the set number of cardiac cycles and then decreasesthe pacing rate by the set amount, as previously discussed, until anintrinsic contraction is detected in the cardiac signal. The intrinsiccontraction is detected by the intrinsic rate detector 650, where theintrinsic rate detector 650 also determines the intrinsic rate with thedetected intrinsic contraction, as previously described. Once theintrinsic rate is determined, the pulse rate controller 644 thenincreases and maintains the pacing rate of the pacing pulses above theintrinsic rate, as previously described.

Electronic communication circuitry 680 is additionally coupled to thecontrol circuitry 630 to allow communication with an external controller688. In one embodiment, the electronic communication circuitry 680includes a data receiver and a data transmitter to send and receive andtransmit signals and cardiac data to and from an external programmer688. In one embodiment, the data receiver and the data transmitterinclude a wire loop antenna to establish a radio frequency telemetriclink, as is known in the art, to receive and transmit signals and datato and from the programmer unit 688.

This application is intended to cover any adaptations or variations ofthe present invention. For example, while atrial arrhythmia has been onefocus of the present subject matter, it is recognized that the sameconcepts and ideas can be applied to the ventricular arrhythmias.Therefore, the foregoing discussion for the present system is notlimited to atrial arrhythmias. It is manifestly intended that thisinvention be limited only by the claims and equivalents thereof.

1. A method, comprising: providing pacing pulses at a pacing rate at an initial value that is well above an intrinsic rate; monitoring for an intrinsic atrial contraction; incrementally decreasing the pacing rate from the initial value until at least one intrinsic atrial contraction is detected; increasing the pacing rate to an adjusted value just above an intrinsic atrial rate; incrementally decreasing the pacing rate from the adjusted value until at least one intrinsic atrial contraction is detected; and increasing the pacing rate to another adjusted value just above the intrinsic atrial rate.
 2. The method of claim 1, comprising determining delivery of an atrial defibrillation shock, wherein providing pacing pulses at the initial value is initiated in response to the atrial defibrillation shock.
 3. The method of claim 1, comprising determining delivery of an atrial defibrillation shock, wherein providing pacing pulses at the initial value is initiated at a first time delay after the atrial defibrillation shock.
 4. The method of claim 1, comprising determining delivery of a cardioversion pulse, wherein providing pacing pulses at the initial value is initiated in response to the cardioversion pulse.
 5. The method of claim 1, comprising determining delivery of a cardioversion pulse, wherein providing pacing pulses at the initial value is initiated at a first time delay after the cardioversion pulse.
 6. The method of claim 1, comprising repeating: incrementally decreasing the pacing rate from the adjusted value until at least one intrinsic atrial contraction is detected; and increasing the pacing rate to another adjusted value just above the intrinsic atrial rate.
 7. The method of claim 6, comprising continuing repeating for a desired time period.
 8. The method of claim 6, comprising continuing repeating until a desired number of intrinsic atrial contractions is detected.
 9. The method of claim 1, further comprising determining the intrinsic atrial rate from the at least one intrinsic atrial contraction.
 10. The method of claim 9, wherein determining the intrinsic atrial rate includes determining the intrinsic atrial rate from at least two intrinsic atrial contractions.
 11. The method of claim 1, wherein incrementally decreasing the pacing rate includes increasing an interval between the pacing pulses by a value in the range of 7.5 to 10 milliseconds.
 12. The method of claim 1, wherein providing pacing pulses at the initial value includes providing pacing pulses at a pacing rate in a range of 100 to 200 pacing pulses per minute.
 13. A method, comprising: determining delivery of an electrical stimulus; providing, in response to the electrical stimulus, pacing pulses at a pacing rate at an initial value that is well above an intrinsic rate; monitoring for an intrinsic atrial contraction; incrementally decreasing the pacing rate from the initial value until at least one intrinsic atrial contraction is detected; increasing the pacing rate to an adjusted value just above an intrinsic atrial rate; incrementally decreasing the pacing rate from the adjusted value until at least one intrinsic atrial contraction is detected; and increasing the pacing rate to another adjusted value just above the intrinsic atrial rate.
 14. The method of claim 13, wherein determining delivery of the electrical stimulus includes determining delivery of an atrial defibrillation shock or a cardioversion pulse.
 15. The method of claim 13, wherein providing pacing pulses at the initial value is initiated at a first time delay after the atrial defibrillation shock.
 16. The method of claim 13, comprising repeating: incrementally decreasing the pacing rate from the adjusted value until at least one intrinsic atrial contraction is detected; and increasing the pacing rate to another adjusted value just above the intrinsic atrial rate.
 17. The method of claim 13, further comprising determining the intrinsic atrial rate from the at least one intrinsic atrial contraction.
 18. The method of claim 17, wherein determining the intrinsic atrial rate includes determining the intrinsic atrial rate from at least two intrinsic atrial contractions.
 19. The method of claim 13, wherein incrementally decreasing the pacing rate includes increasing an interval between the pacing pulses by a value in the range of 7.5 to 10 milliseconds.
 20. The method of claim 13, wherein providing pacing pulses at the initial value includes providing pacing pulses at a pacing rate in a range of 100 to 200 pacing pulses per minute. 